Bone graft materials and methods of use

ABSTRACT

Osteoinductive and osteoconductive compositions for bone graft which utilize less allograft tissue, and methods for their production, are provided. The compositions and methods contain a combination of fibers of demineralized bone matrix from allograft bone and fibers of non-allograft bone material. The fibers of non-allograft bone material comprise non-fibrous demineralized bone matrix particles embedded within or disposed on the fibers of non-allograft bone material. The non-allograft fibers of the composition contain a bone void filler of collagen and one or more ceramics embedded with demineralized bone matrix particles. In some embodiments, the composition also contains a bioactive agent.

BACKGROUND

It is estimated that more than half a million bone grafting procedures are performed in the United States annually with a cost over $2.5 billion. These numbers are expected to double by 2020. Both natural bone and bone substitutes have been used as graft materials. Natural bone may be autograft or allograft. Bone substitutes include natural or synthetic materials such as collagen, silicone, acrylics, calcium phosphate, calcium sulfate, or the like.

There are at least three ways in which a bone graft can help repair a defect. The first is osteogenesis, the formation of new bone within the graft by the presence of bone-forming cells called osteoprogenitor cells. The second is osteoinduction, a process in which molecules contained within the graft (e.g., bone morphogenic proteins and other growth factors) convert progenitor cells into bone-forming cells. The third is osteoconduction, a physical effect by which a matrix often containing graft material acts as a scaffold on which bone and cells in the recipient are able to form. The scaffolds promote the migration, proliferation and differentiation of bone cells for bone regeneration.

Demineralized bone matrix (DBM) has been shown to exhibit the ability to induce and/or conduct the formation of bone. It is therefore desirable to implant and maintain demineralized bone matrix at a site which bone growth is desired.

Bone fiber based-demineralized bone matrices for implantation exhibit improvements in mechanical properties, including cohesiveness, fiber length, fiber diameter or width, fiber aspect ratio, or a combination of multiple variables.

However, in making DBM fibers, there is limited supply due to the limited availability of donor bone and at this time regulations do not permit the pooling of donor bone material. Further, during the manufacture of DBM fibers there is bone material that is not in fiber form but rather particles. Typically, these DBM particles possess random, irregular geometries with bone particles size ranging from about 110 to 850 microns and are usually wasted.

There is a need for DBM compositions and methods that allow osteogenesis, osteoinduction and/or osteoconduction. DBM compositions and methods that can be made from bone material that is not in fiber form and reduces waste of the non-fiber bone material would be beneficial.

SUMMARY

DBM compositions and methods that allow osteogenesis, osteoinduction and/or osteoconduction are provided. DBM compositions and methods are provided where the fiber material is made from non-fiber bone material to reduce wastage of the bone material.

Compositions and methods are provided for an implantable bone graft comprising a combination of fibers of demineralized bone matrix from allograft bone and fibers of non-allograft bone material, the fibers of non-allograft bone material comprising non-fibrous demineralized bone matrix particles embedded within or disposed on the fibers of the non-allograft bone material.

In some embodiments, the fibers of non-allograft bone material comprise a bioerodible polymer and one or more ceramics either alone or in combination. In some embodiments, the fibers of non-allograft bone material comprise ceramics and collagen, hyaluronic acid, chitosan, keratin, and derivatives thereof, either alone or in combination. In some embodiments, the bioerodible polymer is collagen. In some embodiments, the collagen is porous. In other embodiments, the diameter of the fibers of allograft bone and non-allograft bone material is between about 50 μm and about 1 mm. In some embodiments, the diameter of the fibers of allograft bone and non-allograft bone material is between about 75 nm and about 250 nm. In some embodiments, the length of the fibers of the allograft bone and non-allograft material is between about 5 mm and about 30 mm. In some embodiments, the implantable bone graft composition contains a bioactive agent. In some embodiments, the ceramic is a calcium phosphate ceramic and/or a silcon ceramic. In other embodiments, the ceramic is tricalcium phosphate. In some embodiments, the ratio of fibers of demineralized bone matrix from allograft bone to fibers of non-allograft material ranges from about 80:20 to about 70:30, preferably from about 40:60 to about 60:40. In some embodiments the ratio of fibers of demineralized bone matrix from allograft bone to fibers of non-allograft material is about 50:50. In some embodiments, the non-fibrous demineralized bone matrix particles embedded within or disposed on the fibers of non-allograft bone material range in diameter size from between about 50 μm and about 30 mm.

In some embodiments, a method for preparing a composite bone graft composition is provided. The method comprises mixing collagen and ceramic powder to form a slurry, drying the slurry to form a sheet or a block, embedding demineralized bone matrix particles within or disposed on the fibers of collagen and ceramic powder. Obtaining fibers from the sheet or block. Combining those non-allograft fibers obtained, with fibers of demineralized bone matrix from allograft bone. The method may provide for air-drying or alternatively, freeze drying.

In some embodiments, the method comprises obtaining the fibers by shaving, milling, or pressing the sheet or block. In some embodiments, the method comprises adding a binding agent such as glycerol or a bioactive agent or drug. In some embodiments, a method of generating or regenerating bone in a patient in need thereof is provided where the patient is implanted with the implantable composition of allograft and non-allograft fibers.

In some embodiments, a kit for the implantable composition is provided together with instructions for use.

Additional features and advantages of various embodiments will be set forth in part in the description that follows, and in part will be apparent from the description, or may be learned by practice of various embodiments. The objectives and other advantages of various embodiments will be realized and attained by means of the elements and combinations particularly pointed out in the description and appended claims.

DETAILED DESCRIPTION

For the purposes of promoting an understanding of the principles of the disclosure, reference will now be made to certain embodiments and specific language will be used to describe the same. It will nevertheless be understood that no limitation of the scope of the disclosure is thereby intended, such alterations and further modifications in the illustrated device, and such further applications of the principles of the disclosure as described herein being contemplated as would normally occur to one skilled in the art to which the disclosure relates.

For the purposes of this specification and appended claims, unless otherwise indicated, all numbers expressing quantities of ingredients, percentages or proportions of materials, reaction conditions, and other numerical values used in the specification and claims, are to be understood as being modified in all instances by the term “about.” Accordingly, unless indicated to the contrary, the numerical parameters set forth in the following specification and attached claims are approximations that may vary depending upon the desired properties sought to be obtained by the present application. At the very least, and not as an attempt to limit the application of the doctrine of equivalents to the scope of the claims, each numerical parameter should at least be construed in light of the number of reported significant digits and by applying ordinary rounding techniques.

Notwithstanding that the numerical ranges and parameters setting forth the broad scope of the disclosure are approximations, the numerical representations are as precise as possible. Any numerical value, however, inherently contains certain errors necessarily resulting from the standard deviation found in their respective testing measurements. Moreover, all ranges disclosed herein are to be understood to encompass any and all subranges subsumed therein. For example, a range of “1 to 10” includes any and all subranges between (and including) the minimum value of 1 and the maximum value of 10, that is, any and all subranges having a minimum value of equal to or greater than 1 and a maximum value of equal to or less than 10, e.g., 5.5 to 10.

Additionally, unless defined otherwise or apparent from context, all technical and scientific terms used herein have the same meanings as commonly understood by one of ordinary skill in the art to which this disclosure belongs.

Unless explicitly stated or apparent from context, the following terms are phrases have the definitions provided below:

Definitions

It is noted that, as used in this specification and the appended claims, the singular forms “a,” “an,” and “the,” include plural referents unless expressly and unequivocally limited to one referent. Thus, for example, reference to “an allograft” includes one, two, three or more allografts.

The term “biodegradable” includes that all or parts of the carrier and/or implant will degrade over time by the action of enzymes, by hydrolytic action and/or by other similar mechanisms in the human body. In various embodiments, “biodegradable” includes that the carrier and/or implant can break down or degrade within the body to non-toxic components after or while a therapeutic agent has been or is being released. By “bioerodible” it is meant that the carrier and/or implant will erode or degrade over time due, at least in part, to contact with substances found in the surrounding tissue, fluids or by cellular action.

The term “mammal” refers to organisms from the taxonomy class “mammalian,” including but not limited to humans, other primates such as chimpanzees, apes, orangutans and monkeys, rats, mice, cats, dogs, cows, horses, etc.

A “therapeutically effective amount” or “effective amount” is such that when administered, the drug (e.g., growth factor) results in alteration of the biological activity, such as, for example, promotion of bone, cartilage and/or other tissue (e.g., vascular tissue) growth, inhibition of inflammation, reduction or alleviation of pain, improvement in the condition through inhibition of an immunologic response, etc. The dosage administered to a patient can be as single or multiple doses depending upon a variety of factors, including the drug's administered pharmacokinetic properties, the route of administration, patient conditions and characteristics (sex, age, body weight, health, size, etc.), extent of symptoms, concurrent treatments, frequency of treatment and the effect desired. In some embodiments the implant is designed for immediate release. In other embodiments the implant is designed for sustained release. In other embodiments, the implant comprises one or more immediate release surfaces and one or more sustained release surfaces.

The terms “treating” and “treatment” when used in connection with a disease or condition refer to executing a protocol that may include a bone repair procedure, where the bone implant and/or one or more drugs are administered to a patient (human, other normal or otherwise or other mammal), in an effort to alleviate signs or symptoms of the disease or condition or immunological response. Alleviation can occur prior to signs or symptoms of the disease or condition appearing, as well as after their appearance. Thus, treating or treatment includes preventing or prevention of disease or undesirable condition. In addition, treating, treatment, preventing or prevention do not require complete alleviation of signs or symptoms, does not require a cure, and specifically includes protocols that have only a marginal effect on the patient.

The term “bone,” as used herein, refers to bone that is cortical, cancellous or cortico-cancellous of autogenous, allogenic, xenogenic, or transgenic origin.

The term “allograft” refers to a graft of tissue obtained from a donor of the same species as, but with a different genetic make-up from, the recipient, as a tissue transplant between two humans.

The term “autologous” refers to being derived or transferred from the same individual's body, such as for example an autologous bone marrow transplant.

The term “osteoconductive,” as used herein, refers to the ability of a non-osteoinductive substance to serve as a suitable template or substance along which bone may grow.

“Non-allograft bone material” refers to implantable material that is not obtained from allograft bone. Non-allograft bone material can be synthetic material (e.g., ceramic, synthetic polymers, etc.) or non-synthetic non-bone material (e.g., collagen, chitosan, alginate, elastic, etc.). The non-allograft bone material is made into fibers to mimic the allograft bone fibers. The non-allograft bone material can then be made osteogenic, osteoinductive, and/or osteoconductive by, embedding or adding DBM material to the non-allograft bone fibers. This includes DBM in the form of fragments, slices, pellets, shavings, granules, fibers, or powder or the like, which can be coated on, attached to, or embedded in the non-allograft bone fibers.

The term “osteoinductive,” as used herein, refers to the quality of being able to recruit cells from the host that have the potential to stimulate new bone formation. Any material that can induce the formation of ectopic bone in the soft tissue of an animal is considered osteoinductive.

The term “osteoinduction” refers to the ability to stimulate the proliferation and differentiation of pluripotent mesenchymal stem cells (MSCs). In endochondral bone formation, stem cells differentiate into chondroblasts and chondrocytes, laying down a cartilaginous ECM, which subsequently calcifies and is remodeled into lamellar bone. In intramembranous bone formation, the stem cells differentiate directly into osteoblasts, which form bone through direct mechanisms. Osteoinduction can be stimulated by osteogenic growth factors, although some ECM proteins can also drive progenitor cells toward the osteogenic phenotype.

The term “osteoconduction” refers to the ability to stimulate the attachment, migration, and distribution of vascular and osteogenic cells within the graft material. The physical characteristics that affect the graft's osteoconductive activity include porosity, pore size, and three-dimensional architecture. In addition, direct biochemical interactions between matrix proteins and cell surface receptors play a major role in the host's response to the graft material.

The term “osteogenic” refers to the ability of a graft material to produce bone independently. To have direct osteogenic activity, the graft must contain cellular components that directly induce bone formation. For example, an allograft seeded with activated MSCs would have the potential to induce bone formation directly, without recruitment and activation of host MSC populations. Because many osteoconductive allografts also have the ability to bind and deliver bioactive molecules, their osteoinductive potential will be greatly enhanced.

The term “osteoimplant,” as used herein, refers to any bone-derived implant prepared in accordance with the embodiments of this disclosure and, therefore, is intended to include expressions such as bone membrane or bone graft.

The term “patient” refers to a biological system to which a treatment can be administered. A biological system can include, for example, an individual cell, a set of cells (e.g., a cell culture), an organ, or a tissue. Additionally, the term “patient” can refer to animals, including, without limitation, humans.

The term “particles” as utilized herein is intended to include relatively small pieces such as fibers, bundles of loosely connected fibers, threads, narrow strips, thin sheets, chips, shards, powders, etc, that possess regular, irregular or random geometrics and which may, or may not, be completely separated from each other.

The term “demineralized,” as used herein, refers to any material generated by removing mineral material from tissue, e.g., bone tissue. In certain embodiments, the demineralized compositions described herein include preparations containing less than 5%, 4%, 3%, 2% or 1% calcium by weight. Partially demineralized bone (e.g., preparations with greater than 5% calcium by weight but containing less than 100% of the original starting amount of calcium) is also considered within the scope of the disclosure. In some embodiments, partially demineralized bone contains preparations with greater than 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, 80%, 85%, 90%, 95%, 96%, 97%, 98% or 99% of the original starting amount of calcium. In some embodiments, demineralized bone has less than 95% of its original mineral content. In some embodiments, demineralized bone has less than 95%, 90%, 85%, 80%, 75%, 70%, 65%, 60%, 55%, 50%, 45%, 40%, 35%, 30%, 25%, 20%, 15%, 10%, or 5% of its original mineral content. Demineralized is intended to encompass such expressions as “substantially demineralized,” “partially demineralized,” and “fully demineralized.” In some embodiments, part or all of the surface of the bone can be demineralized. For example, part or all of the surface of the allograft can be demineralized to a depth of from about 100 to about 5000 microns, or about 150 microns to about 1000 microns. In some embodiments, part or all of the surface of the allograft can be demineralized to a depth of from about 100, 150, 200, 250, 300, 350, 400, 450, 500, 550, 600, 650, 700, 750, 800, 850, 900, 950, 1000, 1050, 1100, 1150, 1200, 1250, 1300, 1350, 1400, 1450, 1500, 1550, 1600, 1650, 1700, 1750, 1800, 1850, 1900, 1950, 2000, 2050, 2100, 2150, 2200, 2250, 2300, 2350, 2400, 2450, 2500, 2550, 2600, 2650, 2700, 2750, 2800, 2850, 2900, 2950, 3000, 3050, 3100, 3150, 3200, 3250, 3300, 3350, 3400, 3450, 3500, 3550, 3600, 3650, 3700, 3750, 3800, 3850, 3900, 3950, 4000, 4050, 4100, 4150, 4200, 4250, 4300, 4350, 4400, 4450, 4500, 4550, 4600, 4650, 4700, 4750, 4800, 4850, 4900, 4950 to about 5000 microns. If desired, the outer surface of the intervertebral implant can be masked with an acid resistant coating or otherwise treated to selectively demineralize unmasked portions of the outer surface of the intervertebral implant so that the surface demineralization is at discrete positions on the implant.

The term “demineralized bone matrix,” as used herein, refers to any material generated by removing mineral material from bone tissue. In some embodiments, the DBM compositions as used herein include preparations containing less than 5%, 4%, 3%, 2% or 1% calcium by weight.

The term “superficially demineralized,” as used herein, refers to bone-derived elements possessing at least about 90, 91, 92, 93, 94, 95, 96, 97, 98 or 99 weight percent of their original inorganic mineral content. The expression “partially demineralized” as used herein refers to bone-derived elements possessing from about 8 to about 90 weight percent of their original inorganic mineral content. In some embodiments, partially demineralized refers to bone-derived elements possessing from about 8, 10, 12, 14, 16, 18, 20, 22, 24, 26, 28, 30, 32, 34, 36, 38, 40, 42, 44, 46, 48, 50, 52, 54, 56, 58, 60, 62, 64, 66, 68, 70, 72, 74, 76, 78, 80, 82, 84, 86, 88 to about 90 weight percent of their original inorganic mineral content. The expression “fully demineralized” as used herein refers to bone containing less than 8%, 7%, 6%, 5%, 4%, 3%, 2%, 1% of its original mineral context.

The terms “pulverized bone”, “powdered bone” or “bone powder” as used herein, refers to bone particles of a wide range of average particle size ranging from relatively fine powders to coarse grains and even larger chips.

The allograft can comprise bone fibers. Fibers include bone elements whose average length to average thickness ratio or aspect ratio of the fiber is from about 50:1 to about 1000:1. In overall appearance the fibrous bone elements can be described as elongated bone fibers, threads, narrow strips, or thin sheets. Often, where thin sheets are produced, their edges tend to curl up toward each other. The fibrous bone elements can be substantially linear in appearance or they can be coiled to resemble springs. In some embodiments, the elongated bone fibers are of irregular shapes including, for example, linear, serpentine or curved shapes. The elongated bone fibers are preferably demineralized, however, some of the original mineral content may be retained when desirable for a particular embodiment.

“Non-fibrous”, as used herein, refers to elements that have an average width substantially smaller than the average thickness of the fibrous bone element or aspect ratio of less than from about 50:1 to about 1000:1. In some embodiments, the non-fibrous bone elements are shaped in a substantially regular manner or specific configuration, for example, triangular prism, sphere, cube, cylinder and other regular shapes. By contrast, particles such as chips, shards, or powders possess irregular or random geometries. It should be understood that some variation in dimension will occur in the production of the elements of this application and elements demonstrating such variability in dimension are within the scope of this application and are intended to be understood herein as being within the boundaries established by the expressions “mostly irregular” and “mostly regular”. For example, allograft bone fibers will have a fiber shape, while the non-fibrous material will not have a fiber shape but will have a shape such as, for example, triangular prism, sphere, cube, cylinder, square, particle, and other regular or irregular shapes. The non-fibrous material can be material obtained after the fiber has been harvested from the allograft bone. In some embodiments, the non-fibrous, non-allograft material is synthetic and not obtained from allograft bone.

“Pressed bone fibers”, as used herein, refer to bone fibers formed by applying pressure to bone stock. The bone utilized as the starting, or stock, material may range in size from relatively small pieces of bone to bone of such dimensions as to be recognizable as to its anatomical origin. The bone may be substantially fully demineralized, surface demineralized, partially demineralized, or nondemineralized. In general, the pieces or sections of whole bone stock can range from about 1 to about 400 mm, from about 5 to about 100 mm, in median length, from about 0.5 to about 20 mm, or from about 2 to about 10 mm, in median thickness and from about 1 to about 20 mm, or from about 2 to about 10 mm, in median width. Forming bone fibers by pressing results in intact bone fibers of longer length than other methods of producing the elongate bone fibers retaining more of the native collagen structure. The bone may be particulated via pressure applied to the bone, as discussed in U.S. Pat. No. 7,323,193, herein incorporated by reference.

“High porosity”, as used herein refers to having a pore structure that is conducive to cell ingrowth, and the ability to promote cell adhesion, proliferation and differentiation.

“Resorbable”, as used herein, refers to a material that exhibits chemical dissolution when placed in a mammalian body.

“Bioactive agent” or “bioactive compound”, as used herein, refers to a compound or entity that alters, inhibits, activates, or otherwise affects biological or chemical events. For example, bioactive agents may include, but are not limited to, osteogenic or chondrogenic proteins or peptides, anti-AIDS substances, anti-cancer substances, antibiotics, immunosuppressants, anti-viral substances, enzyme inhibitors, hormones, neurotoxins, opioids, hypnotics, anti-histamines, lubricants, tranquilizers, anti-convulsants, muscle relaxants and anti-Parkinson substances, anti-spasmodics and muscle contractants including channel blockers, miotics and anti-cholinergics, anti-glaucoma compounds, anti-parasite and/or anti-protozoal compounds, modulators of cell-extracellular matrix interactions including cell growth inhibitors and antiadhesion molecules, vasodilating agents, inhibitors of DNA, RNA or protein synthesis, anti-hypertensives, analgesics, anti-pyretics, steroidal and non-steroidal anti-inflammatory agents, anti-angiogenic factors, angiogenic factors, anti-secretory factors, anticoagulants and/or antithrombotic agents, local anesthetics, ophthalmics, prostaglandins, anti-depressants, anti-psychotic substances, anti-emetics, and imaging agents. In certain embodiments, the bioactive agent is a drug. In some embodiments, the bioactive agent is a growth factor, cytokine, extracellular matrix molecule or a fragment or derivative thereof, for example, a cell attachment sequence such as RGD.

Reference will now be made in detail to certain embodiments of the disclosure. The disclosure is intended to cover all alternatives, modifications, and equivalents that may be included within the disclosure as defined by the appended claims.

The headings below are not meant to limit the disclosure in any way; embodiments under any one heading may be used in conjunction with embodiments under any other heading.

It will be apparent to those skilled in the art that various modifications and variations can be made to various embodiments described herein without departing from the spirit or scope of the teachings herein. Thus, it is intended that various embodiments cover other modifications and variations of various embodiments within the scope of the present teachings.

DBM compositions and methods that allow osteogenesis, osteoinduction and/or osteoconduction are provided. DBM compositions and methods are provided where the fiber material is made from non-fiber bone material to reduce wastage of the bone material.

Compositions and methods are provided for an implantable bone graft comprising a combination of fibers of demineralized bone matrix from allograft bone and fibers of non-allograft bone material, the fibers of non-allograft bone material comprising non-fibrous demineralized bone matrix particles embedded within or disposed on the fibers of the non-allograft bone material.

The compositions of the present disclosure results in an effective bone grafting product. The bone graft material is resorbed/remodeled and replaced by host bone during the healing process. The synthetic ceramics produce high concentrations of calcium, phosphate and silicon ions that act as a nidus for de-novo bone formation. As the bioerodible polymer degrades faster than the ceramic, more and more osteoinductive DBM particles are exposed. The slower resorbing ceramic acts as a solid surface for stem cells and osteoblasts to attach to and begin laying down new bone.

The bone graft composition of the disclosure has good flexibility and is compression resistant. It is also osteoinductive with the demineralized bone matrix retaining activity. These properties make an excellent bone graft substitute in that it may not break, crack, or deform when implanted in the body. The use of the polymer and ceramics allows for the trapping of the demineralized bone within flexible and strong particles.

The implantable composition is a combination of fibers of demineralized bone matrix from allograft bone and fibers of non-allograft bone material. The fibers of the non-allograft bone material comprise non-fibrous demineralized bone matrix particles embedded within or dispersed on the fibers of the non-allograft bone material.

The fibers of the non-allograft bone material comprises a bioerodible polymer and a synthetic ceramic to which demineralized bone matrix particles are embedded either within and/or on the surface of the non-allograft bone material.

The demineralized bone matrix particles are non-fibrous. In other embodiments, the particles are powders, microspheres, sponges, pastes, gels, and/or granules. In one embodiment, the particles are powders.

In some embodiments, the demineralized bone material particles comprise from about 1 to about 70 micrometers or from about 125 to about 250 micrometers. In some embodiments, the demineralized bone material particles comprise about 1, 2, 4, 6, 8, 10, 12, 14, 16, 18, 20, 22, 24, 26, 28, 30, 32, 34, 36, 38, 40, 42, 44, 46, 48, 50, 52, 54, 56, 58, 60, 62, 64, 66, 68, 70, 72, 74, 76, 78, 80, 82, 84, 86, 88, 90, 92, 94, 96, 98, 100, 102, 104, 106, 108, 110, 112, 114, 116, 118, 120, 122, 124, 126, 128, 130, 132, 134, 136, 138, 140, 142, 144, 146, 148, 150, 152, 154, 156, 158, 160, 162, 164, 166, 168, 170, 172, 174, 176, 178, 180, 182, 184, 186, 188, 190, 192, 194, 196, 198, 200, 202, 204, 206, 208, 210, 212, 214, 216, 218, 220, 222, 224, 226, 228, 230, 232, 234, 236, 238, 240, 242, 244, 246, 248 and/or 250 micrometers.

The ratio of fibers of demineralized bone matrix from allograft material to fibers of non-allograft material ranges from about 20:80 to about 70:30. In one embodiment, the ratio of fibers from allograft material to fibers of non-allograft material ranges from about 40:60 to about 60:40. In one embodiment, the ratio of fibers of demineralized bone matrix from allograft material to fibers of non-allograft material is about 50:50.

The composition has very low immunogenicity and good compatibility.

The present disclosure provides a bone graft composition comprising a bioerodible polymer, one or more ceramics and demineralized bone matrix where the demineralized bone matrix particles are embedded within or coated on the surface of the bioerodible polymer and ceramic particles.

In a further embodiment, the demineralized bone matrix particles are dispersed throughout the bioerodible polymer and ceramic particles. In some embodiments, the demineralized bone matrix particles are dispersed homogeneously (or as near to homogeneously as possible) throughout the polymer and ceramic particles.

DBM particles for use in the present disclosure can be obtained commercially or can be prepared by known techniques. In general, advantageous, osteoinductive DBM materials can be prepared by decalcification of cortical and/or cancellous bone, often by acid extraction. This process can be conducted so as to leave collagen, noncollagenous proteins, and growth factors together in a solid matrix. Methods for preparing such bioactive demineralized bone matrix are known, in respect of which reference can be made to U.S. Pat. Nos. 5,073,373; 5,484,601; and 5,284,655, as examples. DBM products are also available commercially, including for instance, from sources such as Regeneration Technologies, Inc. (Alachua, Fla.), The American Red Cross (Arlington, Va.), and others. For the purposes of this disclosure, any shape and particle size of DBM may be used. This includes DBM in the form of fragments, slices, pellets, shavings, granules, fibers, or powder a well as demineralized whole bones. In various embodiments, the demineralized bone is of a small particle size, and in the form of powder. In certain embodiments, the particulate DBM material can have an average particle size of less than about 100 to about 1000 microns. For instance, the DBM material can have particle sizes in the range of 50 to 850 microns. DBM materials that are solely osteoconductive can be prepared using similar techniques that have been modified or supplemented to remove or inactivate (e.g. by crosslinking or otherwise denaturing) components in the bone matrix responsible for osteoinductivity. Osteoinductive and/or osteoconductive DBM materials used in the present disclosure can be derived from human donor tissue, especially in regard to implant devices intended for use in human subjects.

In regard to the incorporated materials considered on a dry weight basis, the particulate DBM material, which are embedded onto the non-allograft fibers can constitute about 10% to about 50% of the compositions, about 20% to about 40%, and about 25% to about 35% by weight. In various embodiments, particulate DBM material embedded onto the non-allograft fibers can constitute about 10%, 11%, 12%, 13%, 14%, 15%, 16%, 17%, 18%, 19%, 20%, 21%, 22%, 23%, 24%, 25%, 26%, 27%, 28%, 29%, 30%, 31%, 32%, 33%, 34%, 35%, 36%, 37%, 38%, 39%, 40%, 41%, 42%, 43%, 44%, 45%, 46%, 47%, 48%, 49% or about 50% of the compositions. In a similar vein, formulations can contain about 5% to about 30% by weight insoluble collagen particulate on a dry weight basis, more preferably about 8% to about 20%, and most preferably about 10% to about 15%; and can contain the ceramics at a level of about 1% to about 20% on a dry weight basis, about 5% to about 15%, and about 8% to about 12%. It will be understood, however, that other amounts of these materials can be used within the broader aspects of the present disclosure.

In some embodiments, the demineralized bone fibers of allograft bone and fibers of non-allograft bone have an average length to average thickness ratio or aspect ratio of the fibers from about 50:1 to about 1000:1. In overall appearance the elongated demineralized bone fibers can be in the form of threads, narrow strips, and/or thin sheets. The elongated demineralized bone fibers can be substantially linear in appearance or they can be coiled to resemble springs. In some embodiments, the elongated demineralized bone fibers are of irregular shapes including, for example, linear, serpentine and/or curved shapes. The elongated bone fibers can be demineralized however some of the original mineral content may be retained when desirable for a particular embodiment. The bone graft composition may further comprise mineralized bone particles as known in the art.

The bioerodible polymer will exhibit dissolution when placed in a mammalian body and may be hydrophilic (e.g., collagen, hyaluronic acid, polyethylene glycol). Synthetic polymers are suitable according to the present disclosure, as they are biocompatible and available in a range of copolymer ratios to control their degradation.

In some embodiments, hydrophobic polymers (e.g. poly(lactide-co-glycolyde), polyanhydrides) may be used. Alternatively, a combination of hydrophilic and hydrophobic polymers may be used in the bone graft composition of the disclosure.

Exemplary materials may include biopolymers and synthetic polymers such as human skin, human hair, bone, collagen, fat, thin cross-linked sheets containing fibers and/or fibers and chips, polyethylene glycol (PEG), chitosan, alginate sheets, cellulose sheets, hyaluronic acid sheet, as well as copolymer blends of poly (lactide-co-glycolide) PLGA.

In some embodiments, the particles disclosed herein can also include other biocompatible and bioresorbable substances. These materials may include, for example, natural polymers such as proteins and polypeptides, glycosaminoglycans, proteoglycans, elastin, hyaluronic acid, dermatan sulfate, gelatin, or mixtures or composites thereof. Synthetic polymers may also be incorporated into the bone graft composites. These include, for example biodegradable synthetic polymers such as polylactic acid, polyglycolide, polylactic polyglycolic acid copolymers (“PLGA”), polycaprolactone (“PCL”), poly(dioxanone), poly(trimethylene carbonate) copolymers, polyglyconate, poly(propylene fumarate), poly(ethylene terephthalate), poly(butylene terephthalate), polyethylene glycol, polycaprolactone copolymers, polyhydroxybutyrate, polyhydroxyvalerate, tyrosine-derived polycarbonates and any random or (multi-)block copolymers, such as bipolymer, terpolymer, quaterpolymer, etc., that can be polymerized from the monomers related to previously-listed homo- and copolymers.

The bioerodible polymer may have a molecular weight of from about 1,000 to about 30,000 Daltons (Da). In various embodiments, the polymer may have a molecular weight of from about 2,000 to about 10,000 Da. In some embodiments, the polymer may have a molecular weight of from about 2,000 to 4,000 Da or from about 3,000 to 4,000 Da. In some embodiments, the bioerodible polymer may have a molecular weight of 1,000, 2,000, 3,000, 4,000, 5,000, 6,000, 7,000, 8,000, 9,000, 10,000, 11,000, 12,000, 13,000, 14,000, 15,000, 16,000, 17,000, 18,000, 19,000, 20,000, 21,000, 22,000, 23,000, 24,000, 25,000, 26,000, 27,000, 28,000, 29,000 or about 30,000 Da.

In some embodiments, the bioerodible polymer is collagen. Collagen has excellent histocompatibility without antibody formation or graft rejection. Any suitable collagen material may be used, including known collagen materials, or collagen materials as disclosed in U.S. patent application Ser. No. 12/030,181, Filed Feb. 12, 2008, hereby incorporated by reference in its entirety. Various collagen materials can be used, alone or in combination with other materials.

Insoluble collagen material for use in the disclosure can be derived from natural tissue sources, (e.g. xenogenic, allogenic, or autogenic relative to the recipient human or other patient) or recombinantly prepared. Collagens can be subclassified into several different types depending upon their amino acid sequence, carbohydrate content and the presence or absence of disulfide crosslinks. Types I and III collagen are two of the most common subtypes of collagen and may be used in the present disclosure. Type I collagen is present in skin, tendon and bone, whereas Type III collagen is found primarily in skin. The collagen used in compositions of the disclosure can be obtained from skin, bone, tendon, or cartilage and purified by methods well known in the art and industry. Alternatively, the collagen can be purchased from commercial sources.

The collagen can be atelopeptide collagen and/or telopeptide collagen. Still further, either or both of non-fibrillar and fibrillar collagen can be used. Non-fibrillar collagen is collagen that has been solubilized and has not been reconstituted into its native fibrillar form.

Suitable collagen products are available commercially, including for example from Kensey Nash Corporation (Exton, Pa.), which manufactures a fibrous collagen known as Semed F, from bovine hides. Collagen materials derived from bovine hide are also manufactured by Integra Life Science Holding Corporation (Plainsboro, N.J.). Naturally-derived or recombinant human collagen materials are also suitable for use in the disclosure. Illustratively, recombinant human collagen products are available from Fibrogen, Inc. (San Francisco, Calif.).

The solid particulate collagen incorporated into the inventive compositions can be in the form of intact or reconstituted fibers, or randomly-shaped particles, for example. In certain beneficial embodiments, the solid particulate collagen will be in the form of particles derived from a sponge material, for example by randomly fragmenting the sponge material by milling, shredding or other similar operations. Such particulated sponge material can have an average maximum particle diameter of less than about 6 mm, more preferably less than about 3 mm, and advantageously in the range of about 0.5 mm to 2 mm. Such materials can, for example, be obtained by milling or grinding a porous sponge material and sieving the milled or ground material through a screen having openings sized about 6 mm or smaller, desirably about 0.5 mm to about 2 mm. Retch grinders with associated sieves are suitable for these purposes. Other sources of chemically crosslinked, particulate collagen, in fiber, irregular or other shapes, can also be used to significant advantage, and their use is considered to be another aspect of the present disclosure. These crosslinked particulate materials can be provided as starting materials for preparing compositions as disclosed herein, and therefore as incorporated in the device these particles are individually crosslinked. As well, crosslinked solid collagen particles can be used in combination with non-crosslinked collagen in compositions of the disclosure, wherein the non-crosslinked collagen can be solid (insoluble) or soluble collagen, or combinations thereof Such crosslinked and non-crosslinked collagen mixtures can be used, for example, to modulate the residence time of the collagen portion of the implant compositions in vivo.

Suitable crosslinking agents include, but are not limited to, mono- and dialdehydes, including glytaraldehyde and formaldehyde; polyepoxy compounds such as glycerol; sugars such as glucose. In one embodiment, the crosslinking agent is glycerol.

Exemplary collagen particles can be obtained from various collagen sources including human or non-human (bovine, ovine, and/or porcine), as well as recombinant collagen or combinations thereof Examples of suitable collagen include, but are not limited to, human collagen type I, human collagen type II, human collagen type III, human collagen type IV, human collagen type V, human collagen type VI, human collagen type VII, human collagen type VIII, human collagen type IX, human collagen type X, human collagen type XI, human collagen type XII, human collagen type XIII, human collagen type XIV, human collagen type XV, human collagen type XVI, human collagen type XVII, human collagen type XVIII, human collagen type XIX, human collagen type XXI, human collagen type XXII, human collagen type XXIII, human collagen type XXIV, human collagen type XXV, human collagen type XXVI, human collagen type XXVII, and human collagen type XXVIII, or combinations thereof Collagen further may comprise hetero- and homo-trimers of any of the above-recited collagen types. In some embodiments, the collagen comprises hetero- or homo-trimers of human collagen type I, human collagen type II, human collagen type III, or combinations thereof In some embodiments, the collagen is porous.

In some embodiments, the bioerodible polymer may be hyaluronic acid, chitosan, chitin, keratin, cellulose, glycosaminoglycans and derivatives thereof (e.g. esters of hyaluronic acid) or others of synthetic origin which may be used as an alternative to or in combination with collagen.

Proportions of the polymer may be adjusted within reasonably wide ranges depending upon the properties desired and the clinical applications required. The concentration with respect to the ceramics may be dependent on the nature of the polymer as well as the amount of DBM. In some embodiments, the concentration of the polymer may be from about 3 to about 60 weight percent. In some embodiments, the concentration of the polymer may be about 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32, 33, 34, 35, 36, 37, 38, 39, 40, 41, 42, 43, 44, 45, 46, 47, 48, 49, 50, 51, 52, 53, 54, 55, 56, 57, 58, 59 or about 60 weight percent. In some embodiments, the polymer is collagen present in an amount from about 5 to about 30 weight percent. In some embodiments, the polymer is collagen present in an amount of about 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29 or about 30 weight percent. It is well within the ability of the skilled artisan to determine the optimal amount of bioerodible polymer without undue experimentation.

Proportions of the collagen may be adjusted within reasonably wide ranges depending upon the properties desired and the clinical applications required. In some embodiments, more than 40 weight percent of the composite is collagen.

In some embodiments, the particles disclosed herein also include synthetic ceramics that are effective to provide a scaffold for bone growth and which are completely bioresorbable and biocompatible. The synthetic ceramics should provide high local concentrations of calcium, phosphate and silicon ions that act as a nidus for de-novo bone formation. The use of such a resorbable ceramics provides many advantages over alternative conventional materials. For instance, it eliminates the need for post-therapy surgery for removal and degrades in the human body to biocompatible, bioresorbable products.

In some embodiments, the synthetic ceramics disclosed herein may be selected from one or more materials comprising calcium phosphate ceramics or silicon ceramics. Biological glasses such as calcium-silicate-based bioglass, silicon calcium phosphate, tricalcium phosphate (TCP), biphasic calcium phosphate, calcium sulfate, hydroxyapatite, coralline hydroxyapatite, silicon carbide, silicon nitride (Si₃N₄), and biocompatible ceramics may be used. In some embodiments, the ceramic is tri-calcium phosphate or biphasic calcium phosphate and silicon ceramics. In some embodiments, the ceramic is tricalcium phosphate.

In some embodiments, the ceramics are a combination of a calcium phosphate ceramic and a silicon ceramic. In some embodiments, the calcium phosphate ceramic is resorbable biphasic calcium phosphate (BCP) or resorbable tri-calcium phosphate (TCP), most preferably resorbable TCP.

Biphasic calcium phosphate can have a tricalcium phosphate:hydroxyapatite weight ratio of about 50:50 to about 95:5, about 70:30 to about 95:5, about 80:20 to about 90:10, or about 85:15. The mineral material can be a granular particulate having an average particle diameter between about 0.2 and 5.0 mm, between about 0.4 and 3.0 mm, or between about 0.4 and 2.0 mm.

The ceramics of the disclosure may also be oxide ceramics such as alumina (Al₂O₃) or zirconia (ZrO₂) or composite combinations of oxides and non-oxides such as silicon nitride).

The ceramics of the disclosure may be porous and may have pore sizes large enough to permit osteoinduction via invasion of the material by bone forming cells. Examples of porous ceramics are hydroxyapatite and TCP.

The ceramics of the disclosure are nontoxic and bioerodible such that they exhibit chemical dissolution and resorption when placed in a mammalian body.

In some embodiments, the calcium phosphate is in the form of a ceramic but, may also be in the form of a calcium phosphate containing glass or composition.

In some embodiments, calcium phosphate ceramics with improved osteogenic capacity may be used alone or combined with effective amounts of other ceramics such as silicon ceramics. In some embodiments, the ceramics may include allograft cortical or cancellous bone chips.

In a further aspect, the ceramics exhibit measurable dissolutions rates with porous ceramics biograding much more rapidly (degrade at a higher rate) than nonporous ceramics. The porosity of bone is formed by interconnected large pores of approximately 300-1000 μm. The ceramics of the disclosure should have a porosity to fulfill the microstructural requirements for the bone graft bioapplication.

In some embodiments, the non-allograft bone material includes 40-60 weight percent collagen, 20-50 weight percent DBM, and 10-50 weight percent ceramics. In some embodiments, the ratio of DBM particles to collagen and/or ceramics is about 5:1, about 4:1, about 3:1, about 2:1, about 1:1, about 1:5, about 1:4, about 1:3, or about 1:2. In some embodiments, the ratio of DBM particles to collagen and/or ceramics is about 1.5:0.5, about 1:1, or about 0.5:1.5.

In some embodiments, a binding agent or carrier is added to the bone graft composite to impart specific handling characteristics to the composition. Generally, materials for the carrier may be biocompatible in vivo and optionally biodegradable. The carrier may act as a temporary scaffold until replaced completely by new bone. Examples of suitable carriers include, but are not limited to: (i) Polyhydroxy compound, for example, such classes of compounds as the acyclic polyhydric alcohols, non-reducing sugars, sugar alcohols, sugar acids, monosaccarides, disaccharides, water-soluble or water dispersible oligosaccarides, polysaccarides and known derivatives of the foregoing. Specific polyhydroxy compounds include, 1,2-propanediol, glycerol, 1,4,-butylene glycol trimethylolethane, trimethylolpropane, erythritol, pentaerythritol, ethylene glycols, diethylene glycol, triethylene glycol, tetraethylene glycol, propylene glycol, dipropylene glycol; polyoxyethylene-polyoxypropylene copolymer, for example, of the type known and commercially available under the trade names Pluronic and Emkalyx; polyoxyethylene-polyoxypropylene block copolymer, for example, of the type known and commercially available under the trade name Poloxamer; alkylphenolhydroxypolyoxyethylene, for example, of the type known and commercially available under the trade name Triton, polyoxyalkylene glycols such as the polyethylene glycols, xylitol, sorbitol, mannitol, dulcitol, arabinose, xylose, ribose, adonitol, arabitol, inositol, fructose, galactose, glucose, mannose, sorbose, sucrose, maltose, lactose, maltitol, lactitol, stachyose, maltopentaose, cyclomaltohexaose, carrageenan, agar, dextran, alginic acid, guar gum, gum tragacanth, locust bean gum, gum arabic, xanthan gum, amylose, mixtures of any of the foregoing.

(ii) Polyhydroxy ester, for example, liquid and solid monoesters and diesters of glycerol can be used to good effect, the solid esters being dissolved up in a suitable vehicle, for example, propylene glycol, glycerol, polyethylene glycol of 200-1000 molecular weight. Liquid glycerol esters include monacetin and diacetin and solid glycerol esters include such fatty acid monoesters of glycerol as glycerol monolaurate, glyceryl monopalmitate, glyceryl monostearate. In various embodiments, the carrier herein comprises glyceryl monolaurate dissolved in glycerol or a 4:1 to 1:4 weight mixtures of glycerol and propylene glycol, poly (oxyalkylene) glycol ester.

(iii) Fatty alcohol, for example primary alcohols, usually straight chain having from 6 to 13 carbon atoms, including caproic alcohol, caprylic alcohol, undecyl alcohol, lauryl alcohol, and tridecanol.

(iv) Fatty alcohol ester, for example, ethyl hexyl palmitate, isodecyl neopentate, octadodecyl benzoate, and diethyl hexyl maleate.

(v) Fatty acid having from 6 to 11 carbon atoms, for example, hexanoic acid, heptanoic acid, octanoic acid, decanoic acid and undecanoic acid.

(vi) Fatty acid ester, for example, polyoxyethylene-sorbitan-fatty acid esters, for example, mono- and tri-lauryl, palmityl, stearyl, and oleyl esters including of the type available under the trade name Tween from Imperial Chemical Industries; polyoxyethylene fatty acid esters including polyoxyethylene stearic acid esters of the type known and commercially available under the trade name Myrj; propylene glycol mono- and di-fatty acid esters such as propylene glycol dicaprylate; propylene glycol dilaurate, propylene glycol hydroxy stearate, propylene glycol isostearate, propylene glycol laureate, propylene glycol ricinoleate, propylene glycol stearate, and propylene glycol caprylic-capric acid diester available under the trade name Miglyol; mono-, di-, and mono/di-glycerides, such as the esterification products of caprylic or caproic acid with glycerol, for example, of the type known and commercially available under the trade name lmwitor; sorbitan fatty acid esters, or of the type known and commercially available under the trade name Span, including sorbitan-monolauryl,-monopalmityl, -monostearyl, -tristearyl, -monooleyl and triolcylesters; monoglycerides, for example, glycerol monooleate, glycerol monopalmitate and glycerol monostearate, for example as known and commercially available under the trade names Myvatex, Myvaplex and Myverol, and acetylated, for example, mono- and di-acetylated monoglycerides, for example, as known and commercially available under the trade name Myvacet; isobutyl tallowate, n-butylstearate, n-butyl oleate, and n-propyl oleate.

(vii) Liquid silicone, for example, polyalkyl siloxanes such as polymethyl siloxane and poly (dimethyl siloxane) and polyalkyl arylsiloxane.

In some embodiments of the implantable composition of this application, the liquid carrier or binding agent is a liquid polyhydroxy compound, liquid polyhydroxy compound derivative, liquid solution of solid polyhydroxy compound, liquid solution of solid polyhydroxy compound derivative or mixtures thereof. If necessary or desirable, in some embodiments, the liquid carrier can be dissolved or diluted with an appropriate solvent such that when combined with the elongated demineralized bone fibers described herein a composition capable of being shaped or packed into a coherent mass which retains its shape and volume over the relatively long term, until the bone formation and remodeling process is completed, is provided. Thus, the polyhydroxy compound or polyhydroxy derivatives can be a liquid in the pure or highly concentrated state at ambient temperature, from about 15° C. to about 50° C., or it can be a solid or semi-solid at this temperature in which case it becomes necessary to dissolve the material in a solvent such as water, physiological saline, ethanol, glycerol, glucose, propylene glycol, polyethylene glycol of from 200-1000 molecular weight, or polyvinyl alcohol. In other embodiments, the liquid carrier can be made up of one or more liquid polyhydroxy compounds or derivatives in solution with one or more solid polyhdroxy compounds or derivatives.

The implantable composition may be configured to be moldable, extrudable, or substantially solid. The implantable composition may be configured to substantially retain its shape in water for a period of time. The implantable composition may form an osteoimplant useful in clinical applications. Suitable carriers may include surface demineralized bone; mineralized bone; nondemineralized cancellous scaffolds; demineralized cancellous scaffolds; cancellous chips; particulate, demineralized, guanidine extracted, species-specific (allogenic) bone; specially treated particulate, protein extracted, demineralized, xenogenic bone; collagen; synthetic hydroxyapatites; synthetic calcium phosphate materials; tricalcium phosphate, sintered hydroxyapatite, settable hydroxyapatite; polylactide polymers; polyglycolide polymers, polylactide-co-glycolide copolymers; tyrosine polycarbonate; calcium sulfate; collagen sheets; settable calcium phosphate; polymeric cements; settable poly vinyl alcohols, polyurethanes; resorbable polymers; and other large polymers; liquid settable polymers; and other biocompatible settable materials. The carrier may further comprise a polyol (including glycerol or other polyhydroxy compound), a polysaccharide (including starches), a hydrogel (including alginate, chitosan, dextran, pluronics, N,O-carboxymethylchitosan glucosamine (NOCC)), hydrolyzed cellulose, or a polymer (including polyethylene glycol). In embodiments wherein chitosan is used as a carrier, the chitosan may be dissolved using known methods including in water, in mildly acidic aqueous solutions, in acidic solutions.

The carrier or binding agent may further comprise a hydrogel such as hyaluronic acid, dextran, pluronic block copolymers of polyethylene oxide and polypropylene, and others. Suitable polyhodroxy compounds include such classes of compounds as acyclic polyhydric alcohols, non-reducing sugars, sugar alcohols, sugar acids, monosaccharides, disaccharides, water-soluble or water dispersible oligosaccharides, polysaccharides and known derivatives of the foregoing. An example carrier comprises glyceryl monolaurate dissolved in glycerol or a 4:1 to 1:4 weight mixture of glycerol and propylene glycol. Settable materials may be used, and they may set up either in situ, or prior to implantation. Optionally, xenogenic bone powder carriers also may be treated with proteases such as trypsin. Xenogenic carriers may be treated with one or more fibril modifying agents to increase the intraparticle intrusion volume (porosity) and surface area. Useful agents include solvents such as dichloromethane, trichloroacetic acid, acetonitrile and acids such as trifluoroacetic acid and hydrogen fluoride. The choice of carrier may depend on the desired characteristics of the composition. In some embodiments, a lubricant, such as water, glycerol, or polyethylene glycol may be added.

Any suitable shape, size, and porosity of carrier may be used. In some embodiments, the carrier or binding agent may be settable and/or injectable. Such carrier may be, for example, a polymeric cement, a suitable settable calcium phosphate, a settable poly vinyl alcohol, a polyurethane, or a liquid settable polymer. Hydrogel carriers may additionally impart improved spatial properties, such as handling and packing properties, to the osteoconductive composition. An injectable carrier may be desirable where the composition is used with a containment device. In addition, selected materials must be biocompatible in vivo and optionally biodegradable. In some uses, the carrier acts as a temporary scaffold until replaced by new bone. Polylactic acid (PLA), polyglycolic acid (PGA), and various combinations have different dissolution rates in vivo. In bone, the dissolution rates can vary according to whether the composition is placed in cortical or trabecular bone.

In certain embodiments, the carrier or binding agent may comprise a shape-retaining solid made of loosely adhered particulate material with collagen. It may alternatively comprise a molded, porous solid, a monolithic solid, or an aggregate of close-packed particles held in place by surrounding tissue. Masticated muscle or other tissue may also be used. Large allogenic bone implants may act as a carrier, for example where their marrow cavities are cleaned and packed with DBM and, optionally, the osteoinductive factors. In some embodiments, the carrier or binding agent is glycerol.

In various embodiments, the carrier or binding agent comprises an osteoinductive material such as a mineralized particulated material, osteoinductive growth factors, or partially demineralized bone. The mineralized particulated material may be TCP, hydroxyapatite, mineral recovered from bones, surface demineralized bone fiber, or other material. The osteoinductive material may be combined with a further carrier such as starch or glycerol. Accordingly, in some embodiments, the bone matrix may act as a carrier for the tissue-derived extract.

Settable material may be used, and they may set up either in situ or prior to implantation. The bone fibers and carrier (or delivery or support system) together form an osteoimplant useful in clinical applications.

In some embodiments, the particles may also contain other beneficial substances including for example preservatives, cosolvents, suspending agents, viscosity enhancing agents, ionic strength and osmolality adjusters and/or other excipients. Suitable buffering agents can also be used an include but are not limited to alkaline earth metal carbonates, phosphates, bicarbonates, citrates, borates, acetates, succinates, or others. Illustrative-specific buffering agents include for instance sodium phosphate, sodium citrate, sodium borate, sodium acetate, sodium bicarbonate, sodium carbonate, and sodium tromethanine (TRIS). These agents can be included in amounts that are effective to maintain the pH of the system at a biologically acceptable level, for instance maintaining a pH between about 6 and about 8 and preferably near neutral.

The bone graft composite of the disclosure may be used alone as scaffolds of bone tissue engineering for repair, augmentation or replacement of bone tissue or as carriers for biologically active ingredients.

One of more biologically active ingredients may be added to the resulting composition. These active ingredients may or may not be related to the bone repair capabilities of the composition. Suitable active ingredients hemostatic agents, bone morphogenic proteins (BMPs), genes, growth differentiation factors (GDFs), or other non-collagenic proteins such as TGF-β, PDGF, ostropontin, osteonectin, cytokines, and the like.

In one embodiment, the composition may include at least one BMPs, which are a class of proteins thought to have osteoinductive or growth-promoting activities on endogenous bone tissue, or function as pro-collagen precursors. Known members of the BMP family include, but are not limited to, BMP-1, BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, BMP-7, BMP-8, BMP-9, BMP-10, BMP-11, BMP-12, BMP-13, BMP-15, BMP-16, BMP-17, BMP-18 as well as polynucleotides or polypeptides thereof, as well as mature polypeptides or polynucleotides encoding the same.

BMPs utilized as osteoinductive agents comprise one or more of BMP-1; BMP-2; BMP-3; BMP-4; BMP-5; BMP-6; BMP-7; BMP-8; BMP-9; BMP-10; BMP-11; BMP-12; BMP-13; BMP-15; BMP-16; BMP-17; or BMP-18; as well as any combination of one or more of these BMPs, including full length BMPs or fragments thereof, or combinations thereof, either as polypeptides or polynucleotides encoding the polypeptide fragments of all of the recited BMPs. The isolated BMP osteoinductive agents may be administered as polynucleotides, polypeptides, full length protein or combinations thereof

In another embodiment, the particles may include one or more Growth Differentiation Factors (“GDFs”) disposed in the compartment or disposed on or in one or more surfaces of a covering. Known GDFs include, but are not limited to, GDF-1, GDF-2, GDF-3, GDF-7, GDF-10, GDF-11, and GDF-15. For example, GDFs useful as isolated osteoinductive agents include, but are not limited to, the following GDFs: GDF-1 polynucleotides or polypeptides corresponding to GenBank Accession Numbers M62302, AAA58501, and AAB94786, as well as mature GDF-1 polypeptides or polynucleotides encoding the same. GDF-2 polynucleotides or polypeptides corresponding to GenBank Accession Numbers BC069643, BC074921, Q9UK05, AAH69643, or AAH74921, as well as mature GDF-2 polypeptides or polynucleotides encoding the same. GDF-3 polynucleotides or polypeptides corresponding to GenBank Accession Numbers AF263538, BCO30959, AAF91389, AAQ89234, or Q9NR23, as well as mature GDF-3 polypeptides or polynucleotides encoding the same. GDF-7 polynucleotides or polypeptides corresponding to GenBank Accession Numbers AB158468, AF522369, AAP97720, or Q7Z4P5, as well as mature GDF-7 polypeptides or polynucleotides encoding the same. GDF-10 polynucleotides or polypeptides corresponding to GenBank Accession Numbers BCO28237 or AAH28237, as well as mature GDF-10 polypeptides or polynucleotides encoding the same.

GDF-11 polynucleotides or polypeptides corresponding to GenBank Accession Numbers AF100907, NP005802 or 095390, as well as mature GDF-11 polypeptides or polynucleotides encoding the same. GDF-15 polynucleotides or polypeptides corresponding to GenBank Accession Numbers BC008962, BC000529, AAH00529, or NP004855, as well as mature GDF-15 polypeptides or polynucleotides encoding the same.

In some embodiments, the implantable composition contains other bioactive agents which can be delivered with materials of the disclosure. In certain embodiments, the bioactive agent is a drug. These bioactive agents may include, for example, antimicrobials, antibiotics, antimyobacterial, antifungals, antivirals, antineoplastic agents, antitumor agents, agents affecting the immune response, blood calcium regulators, agents useful in glucose regulation, anticoagulants, antithrombotics, antihyperlipidemic agents, cardiac drugs, thyromimetic and antithyroid drugs, adrenergics, antihypertensive agents, cholinergic, anticholinergics, antispasmodics, antiulcer agents, skeletal and smooth muscle relaxants, prostaglandins, general inhibitors of the allergic response, antihistamines, local anesthetics, analgesics, narcotic antagonists, antitussives, sedative-hypnotic agents, anticonvulsants, antipsychotics, anti-anxiety agents, antidepressant agents, anorexigenics, non-steroidal anti-inflammatory agents, steroidal anti-inflammatory agents, antioxidants, vaso-active agents, bone-active agents, osteogenic factors, antiarthritics, and diagnostic agents.

A more complete listing of bioactive agents and specific drugs suitable for use in the present disclosure may be found in “The Merck Index: An Encyclopedia of Chemicals, Drugs, and Biologicals,” Edited by Susan Budavari, et al.; and the United States Pharmacopoeia/National Formulary XXXVII/XXXII, published by the United States Pharmacopeial Convention, Inc., Rockville, Md., 2013, each of which is incorporated herein by reference.

Bioactive agents may also be provided by incorporation into the implantable composition. Bioactive agents such as those described herein can be incorporated homogeneously or regionally into the implant material by simple admixture or otherwise. Further, they may be incorporated alone or in conjunction with another carrier form or medium such as microspheres or another microparticulate formulation. Suitable techniques for forming microparticles are well known in the art, and can be used to entrain or encapsulate bioactive agents, whereafter the microparticles can be dispersed within the bone graft composite upon or after its preparation.

It will be appreciated that the amount of additive used will vary depending upon the type of additive, the specific activity of the particular additive preparation employed, and the intended use of the composition. The desired amount is readily determinable by the user.

Any of a variety of medically and/or surgically useful substances can be incorporated in, or associated with, the allograft bone material or non-allograft bone material either before, during, or after preparation of the implantable composition. Thus, for example when the non-allograft bone material is used, one or more of such substances may be introduced into the non-allograft bone fibers, for example, by soaking or immersing these bone fibers in a solution or dispersion of the desired substance(s).

All the composite materials according to the present disclosure can be loaded with bone marrow cells taken from the patient directly in the operating theatre while undergoing the type of orthopaedic surgery that requires their application, or a few days before the graft is due to be performed, to allow the purification and expansion in vitro of the mesenchymal cells in the marrow, so that these can then be loaded into the structure that is the subject of the present disclosure, either undifferentiated and/or partially or completely differentiated into osteoblasts/osteocytes.

Alternatively, the implantable composition can also be loaded with allogenic bone marrow cells, possibly purified, expanded and differentiated in vitro. In a further aspect, the bone regeneration scaffold further comprises stem cells, osteogenic cells and/or osteoprogenic cells.

The method of regenerating bone in a subject in need thereof, comprises the steps of providing the subject with the implantable composition according to the disclosure. The implantable composition will generally be implanted by surgery. The surgical procedures to implant the composition may be similar to the procedures usually used by the skilled surgeon when implanting other types of bone graft materials.

Illustrative bone repair sites that can be treated with implantable compositions of the disclosure include, for instance, those resulting from injury, defects brought about during the course of surgery, infection, malignancy or developmental malformation. The composite bone graft compositions can be used in a wide variety of orthopedic, periodontal, neurosurgical and oral and maxillofacial surgical procedures including, but not limited to the repair of simple and compound fractures and non-unions; external and internal fixations; joint reconstructions such as arthrodesis; general arthroplasty; cup arthroplasty of the hip; femoral and humeral head replacement; femoral head surface replacement and total joint replacement; repairs of the vertebral column including spinal fusion and internal fixation; tumor surgery, e.g., deficit filing; discectomy; laminectomy; excision of spinal cord tumors; anterior cervical and thoracic operations; repairs of spinal injuries; scoliosis, lordosis and kyphosis treatments; intermaxillary fixation of fractures; mentoplasty; temporomandibular joint replacement; alveolar ridge augmentation and reconstruction; inlay osteoimplants; implant placement and revision; sinus lifts; cosmetic enhancement; etc. Specific bones which can be repaired or replaced with the composite bone graft compositions or an implant comprising the compositions include, but are not limited to the ethmoid; frontal; nasal; occipital; parietal; temporal; mandible; maxilla; zygomatic; cervical vertebra; thoracic vertebra; lumbar vertebra; sacrum; rib; sternum; clavicle; scapula; humerus; radius; ulna; carpal bones; metacarpal bones; phalanges; ilium; ischium; pubis; femur; tibia; fibula; patella; calcaneus; tarsal and metatarsal bones.

In accordance with certain aspects of the disclosure, composite bone graft compositions of the disclosure can be used as bone void fillers, or can be incorporated in, on or around a load bearing implants such as spinal implants, hip implants (e.g. in or around implant stems and/or behind acetabular cups), knee implants (e.g. in or around stems). In some embodiments, the implantable compositions of the disclosure can be incorporated in, on or around a load-bearing spinal implant device having a compressive strength of at least about 10000 N, such as a fusion cage, dowel, or other device potentially having a pocket, chamber or other cavity for containing an osteoinductive composition, and used in a spinal fusion such as an interbody fusion. One illustrative such use is in conjunction with a load-bearing interbody spinal spacer to achieve interbody fusion. In these applications, the implantable composition can be placed in and/or around the spacer to facilitate the fusion.

Methods for preparing DBM are well known in the art as described, e.g. U.S. Pat. No. 5,314,476, 5,507,813, 5,073,373, and 5,405,390, each incorporated herein by reference. Methods for preparing ceramic powders of calcium phosphate and/or hydroxyapatite are described, e,g, in U.S. Pat. No. 4,202,055 and 4,713,076, each incorporated herein by reference.

The present application also provides a medical kit for preparing the implantable compositions or the disclosure for treating a patient, the kit including at least a delivery system comprising a medical implant device as described above and a package enclosing the medical implant device in a sterile condition. Such kits can include a dried material containing the solid ingredients of the composition along with an aqueous medium or other biocompatible wetting liquid for combination with the dried material to form a malleable wetted material, or can include the formulated, wetted malleable implant material in a suitable container such as a syringe or vial (e.g. terminally sterilized), and/or another item such as a load-bearing implant (e.g., a spinal spacer), and/or a transfer device such as a syringe, and/or a therapeutic substance, for example an osteogenic substance such as a BMP. In one specific form, such a medical kit can include a dried material, such as a particulate or dried body, a BMP in lyophilized form (e.g., rhBMP-2), and an aqueous medium for reconstitution of the BMP to prepare an aqueous formulation that can then be added to the dried material in the process of preparing the composite bone graft composition of the disclosure.

The implantable composition can be delivered in delivery systems including mesh coverings for administration at surgical sites. In some embodiments the delivery system comprises at least one compartment containing the implantable composition disclosed herein.

The covering may comprise a structural material and, in some embodiments, a functional material. The structural material may comprise a mesh material, a polymeric material, or other. The functional material may comprise, for example, a radiopaque material, a bacteriocidal material, or other material.

In some embodiments, the covering includes a hemostatic agent within the compartment with the bone replacement material or the hemostatic agent may be disposed in or on one or more surfaces of the covering and/or compartments of the covering.

Hemostatic agents include, but are not limited to, prothrombin, thrombin, fibrin, fibronectin, Factor X/Xa, Factor VII/VIIa, Factor IX/IXa, Factor XI/XIa, Factor XII/XIIa, Factor XIII, Factor VIII, vitronectin, tissue factor, proteolytic enzyme obtainable from snake venom such as batroxobin, von Willebrand Factor, plasminogen activator inhibitor, platelet activating agents, synthetic peptides having hemostatic activity, collagen particles, derivatives of the above or any combination thereof These hemostatic agents can enhance clotting. In some embodiments, the hemostatic agent comprises gelatins, collagens, oxidized celluloses, thrombin and fibrin sealants, chitosan, synthetic glues, glutaraldehyde-based glues, or a combination thereof. In some embodiments, the hemostatic agent includes collagen particles. Typically, the collagen particles have a mean diameter within the range of from around 5 microns to around 1000 microns, more typically from around 50 microns to around 500 microns. In some embodiments, the collagen particles have a mean diameter of about 100 microns to about 200 microns.

In various embodiments, in accordance with the specific application for which the covering is being used, the covering may be rigid, may be flexible, may be non-elastic, or may be elastic. The covering material may be braided, woven, non-woven shape memory, particulate, threaded, porous, or non-porous. In some embodiments, the covering comprises a pouch with demineralized bone material disposed in the pouch uniformly or in discrete positions within the pouch.

The covering may participate in, control, or otherwise adjust the release of the substance. For example, the covering may act as a selectively permeable membrane and/or may be porous, with the level of porosity being related to the nature of the substances inside the covering. Thus, the material for and configuration of the covering may be selected or adjusted based on desired release characteristics. Specific properties that may be adjusted include thickness, permeability, porosity, strength, flexibility, elasticity, and others of the covering material. It is to be appreciated that some of these properties may depend on others. For example, the thickness and porosity of the material may contribute to its strength, flexibility, and elasticity.

In some embodiments, the covering may be porous to fluid and/or cells, may be biocompatible, and may be resistant to rupture (including should the substance provided therein swell). In some embodiments, the covering with the substance provided therein may be loadbearing. The covering may be resorbable or non-resorbable. The covering may provide increased handling properties, may have irrigation resistance, and/or may support cellular penetration. Flexibility of the covering may be selected to suit particular applications. In some applications, it may be desirable to have a flexible covering.

If the covering is made from a resorbable material, the covering degrades and disappears after a period of time. If the covering is not made of a resorbable material, the covering remains in the body. Tissue ingrowth may occur to bind the host tissue to the substance provided within the covering. Tissue ingrowth through and around the covering, between the host tissue and the substance provided within the covering, may be promoted via openings in the covering.

In various embodiments, the covering may comprise a porous material or a mesh material. The size of the pores of the covering may be designed to permit cellular infiltration (approximately several microns to several millimeters), but may also be designed specifically to exclude cells for the inside of the covering (e.g., approximately 0.45 microns) and only allow diffusion of small molecules (proteins and hormones). Thus, the covering may act to control access to the interior of the delivery system by cells. In embodiments comprising more than one compartment, characteristics of the covering material may be varied between compartments. Generally, the porosity, flexibility, strength, or any other characteristic of one compartment may vary from that characteristic of the other compartment.

The covering may be formed of a resorbable or nonresorbable, natural or synthetic biocompatible material. In some embodiments, more than one material may be used, including as multiple layers. For example, in an embodiment comprising two compartments, one or more materials may be used for the first compartment and a different material or materials may be used for the second compartment. For example, one compartment or portions thereof may be made of material or materials that provide a desired property or properties relative to other compartments or portions thereof, such as increased or decreased resorbability or stiffness, or the different compartments or portions thereof may be imparted with different drug delivery properties, etc. Alternatively, all compartments may comprise the same material or mixtures of materials. Where the characteristics of the material are varied between compartments, or over the surface of a single compartment, the pores of the first compartment or portion thereof may be larger than the pores of the second compartment.

The covering may comprise any suitable structure for delivering a substance in vivo. Thus, as described, the covering may comprise a mesh. In other embodiments, the covering may comprise a polymeric structure with a chamber provided therein. The chamber may be filled with a substance for delivering in vivo, such as autograft, demineralized bone matrix, or others disclosed herein.

In some embodiments, the covering may expand when placed in the body. Expansion can be provided in at least two ways: the covering may be compressed such that the covering expands when placed in the body or the covering may be made of a material that expands when it comes in contact with water or other bodily fluids, either by way of liquid absorption, or by stretching when the materials inside it absorb liquid and themselves expand. In some embodiments, the covering may comprise a shape memory material such as copper-zinc-aluminum-nickel alloy, copper-aluminum-nickel alloy, or nickel-titanium (NiTi) alloy. Reinforcing materials such as cortical bone, calcium phosphates, may also be incorporated into the structure of the covering to reinforce it.

The covering may be configured for specific compressive strength and rigidity by adjusting density and resorption time of the covering. In some embodiments, a coating may be provided over the covering. For example, the coating may be a compound of poly-L-lactide, of polyglycolic acid, or their polymers. The coating may be selected such that it has a resorption time wherein it is resorbed by the body and the material within the covering is permitted to exit through openings in the covering.

A covering according to an aspect of the present application may comprise at least one of bioerodible polymers, bioabsorbable polymers, biodegradable biopolymers, synthetic polymers, copolymers and copolymer blends or combinations thereof Exemplary materials may include biopolymers and synthetic polymers such as human skin, human hair, bone sheets, collagen, fat, thin cross-linked sheets containing fibers and/or fibers and chips, degradable sheets made from polyethylene glycol (PEG), chitosan sheets, alginate sheets, cellulose sheets, hyaluronic acid sheet, as well as copolymer blends of poly (lactide-co-glycolide) PLGA.

Advantageously, a covering according to an aspect of the present application utilizes polymer materials, which provide increased shelf life and further impart and/or improve moisture and/or radiation resistance. Accordingly, a covering provides improved stability, is resistant to environmental degradation, and provides increased durability to e.g., sterilization procedures.

Exemplary materials may include polymeric material (for example, see U.S. Pat. Nos. 6,696,073, 6,478,825, 6,440,444, and 6,294,187 and U.S. Patent Publications Nos. 2006/0216323 and 2005/0251267, all herein incorporated by reference in their entirety); woven material and braided material (for example, see U.S. Patent Publication No. 2005/0283255, herein incorporated by reference in its entirety); non-woven; shape memory material; using outer particles to contain inner particles; attach particles to threads; add porosity to mesh fibers; non-porous materials; non-porous materials. In some embodiments, materials may be used for portions of the covering, such as for a compartment of the covering, which may be substantially impenetrable.

In some embodiments, the covering may comprise a mesh material. Suitable mesh materials include natural materials, synthetic polymeric resorbable materials, synthetic polymeric non-resorbable materials, and other materials. Natural mesh materials include silk, extracellular matrix (such as DBM, collagen, ligament, tendon tissue, or other), silk-elastin, elastin, collagen, and cellulose. Synthetic polymeric resorbable materials include poly(lactic acid) (PLA), poly(glycolic acid) (PGA), poly(lactic acid-glycolic acid) (PLGA), polydioxanone, PVA, polyurethanes, polycarbonates, and others. Other suitable materials include carbon fiber, metal fiber, and various meshes. In other embodiments, the covering may comprise non-woven material such as spun cocoon or shape memory materials having a coil shape or shape memory alloys.

Generally, the covering may be formed of any natural or synthetic structure (tissue, protein, carbohydrate) that can be used to form a covering configuration. Thus, the covering may be formed of a polymer (such as polyalkylenes (e.g., polyethylenes, polypropylenes, etc.), polyamides, polyesters, poly(glaxanone), poly(orthoesters), poly(pyrolicacid), poly(phosphazenes), polycarbonate, other bioabsorbable polymer such as Dacron or other known surgical plastics, a natural biologically derived material such as collagen, gelatin, chitosan, alginate, a ceramic (with bone-growth enhancers, hydroxyapatite, etc.), PEEK (polyether-etherketone), dessicated biodegradable material, metal, composite materials, a biocompatible textile (e.g., cotton, silk, linen), extracellular matrix components, tissues, or composites of synthetic and natural materials, or other. Various collagen materials can be used, alone or in combination with other materials, including collagen sutures and threads. Any suitable collagen material may be used, including known collagen materials, or collagen materials as disclosed in U.S. patent application Ser. No. 12/030,181, filed Feb. 12, 2008, hereby incorporated by reference in its entirety, which discloses collagen materials that may be used for forming a covering. Some examples include polymer or collagen threads woven, or knitted into a mesh. Other suitable materials include thin polymer sheets molded in the presence of a porogen and having underwent leaching; polymer sheets or naturally derived sheets such as fascia and other collagen materials, small intestinal submucosa, or urinary bladder epithelium, the sheets being punctured to introduce porosity; specific shapes printed using available or future printing technologies; naturally secreted materials such as bacterial cellulose grown within specific molds.

In some embodiments, mesh fibers may be treated to impart porosity to the fibers. This may be done, for example, to PLA, PLGA, PGA, and other fibers. One suitable method for treating the mesh fibers comprises supercritical carbon dioxide treatment to partially solubilize the particles. This treatment may further be carried out for viral inactivation. Another suitable method for treating the mesh fibers comprises explosive decompression. Explosive decompression generates porosity and leads to controlled permeability. The mesh material further may be loaded with cells, growth factors, or bioactive agents.

In further embodiments, fibers of a mesh material may be treated such as by having particles adhered thereto. The particles may be, for example, bone particles. Thus, in one embodiment, the covering may comprise a plurality of threads formed into a fabric. The threads may have particles adhered thereto. For example, the threads may have particles strung on the thread. In an alternative embodiment, the covering may be formed of a material and the material may be coated with particles.

In yet other embodiments, the covering may comprise a non-porous material, which may be permeable. A non-porous material may be used for later (or delayed) delivery of a substance provided therein. Such substance may comprise, for example, cells, growth factors, or bone morphogenetic proteins. Accordingly, in one embodiment, a delivery system for delayed delivery of cells, growth factors, or bone morphogenetic proteins is provided comprising a non-porous covering.

In particular, in various embodiments, the device may comprise a bioerodible, a bioabsorbable, and/or a biodegradable biopolymer that may provide immediate release, or sustained release of the implantable composition. Examples of suitable sustained release biopolymers include but are not limited to poly (alpha-hydroxy acids), poly (lactide-co-glycolide) (PLGA), polylactide (PLA), polyglycolide (PG), polyethylene glycol (PEG) conjugates of poly (alpha-hydroxy acids), poly(orthoester)s (POE), polyaspirins, polyphosphagenes, collagen, starch, pre-gelatinized starch, hyaluronic acid, chitosans, gelatin, alginates, albumin, fibrin, vitamin E compounds, such as alpha tocopheryl acetate, d-alpha tocopheryl succinate, D,L-lactide, or L-lactide,-caprolactone, dextrans, vinylpyrrolidone, polyvinyl alcohol (PVA), PVA-g-PLGA, PEGT-PBT copolymer (polyactive), PEO-PPO-PAA copolymers, PLGA-PEO-PLGA, PEG-PLG, PLA-PLGA, poloxamer 407, PEG-PLGA-PEG triblock copolymers, SAIB (sucrose acetate isobutyrate) or combinations thereof As persons of ordinary skill are aware, mPEG and/or PEG may be used as a plasticizer for PLGA, but other polymers/excipients may be used to achieve the same effect. mPEG imparts malleability to the resulting formulations. In some embodiments, these biopolymers may also be coated on the implantable composition to provide the desired release profile. In some embodiments, the coating thickness may be thin, for example, from about 5, 10, 15, 20, 25, 30, 35, 40, 45 or 50 microns to thicker coatings 60, 65, 70, 75, 80, 85, 90, 95, 100 microns to delay release of the substance from the medical device. In some embodiments, the range of the coating on the medical device ranges from about 5 microns to about 250 microns or 5 microns to about 200 microns to delay release from the medical device.

In various embodiments, the implantable composition also comprises poly(lactide-co-glycolide) (PLGA), polylactide (PLA), polyglycolide (PGA), D-lactide, D,L-lactide, L-lactide, D,L-lactide-co-E-caprolactone, D,L-lactide-co-glycolide-co-E-caprolactone, L-lactide-co-ε-caprolactone or a combination thereof.

The covering material may have functional characteristics. Alternatively, other materials having functional characteristics may be incorporated into the covering. Functional characteristics may include radiopacity, bacteriocidity, source for released materials, tackiness, etc. Such characteristics may be imparted substantially throughout the covering or at only certain positions or portions of the covering.

Suitable radiopaque materials include, for example, ceramics, mineralized bone, ceramics/calcium phosphates/calcium sulfates, metal particles, fibers, and iodinated polymer. Polymeric materials may be used to form the covering and be made radiopaque by iodinating them. Other techniques for incorporating a biocompatible metal or metal salt into a polymer to increase radiopacity of the polymer may also be used. Suitable bacteriocidal materials may include, for example, trace metallic elements. In some embodiments, trace metallic elements may also encourage bone growth.

Functional material, such as radiopaque markers, may be provided at one or more locations on the covering or may be provided substantially throughout the covering. Thus, for example, in a tubular covering, a radiopaque marker may be provided at a tip of the tubular covering. Such marker may facilitate placement of the covering. Radiopaque materials may be incorporated into the covering and/or into the substance for delivery by the covering. Further, radiopaque materials may be provided at only some locations on the covering such that visualization of those locations provides indication of the orientation of the covering in vivo.

The covering itself may be designed to release materials during degradation of the covering material. Thus, bone morphogenic proteins (BMPs), growth factors, antibiotics, angiogenesis promoting materials, bioactive agents, or other actively releasing materials may be incorporated into the covering material such that as the covering material is degraded in the body, the actively releasing material is released. For example, an actively releasing material may be incorporated into a biodegradable polymer covering such as one manufactured of a biodegradable polyester such as poly(lactic acid) (PLA), poly(glycolic acid) (PGA), poly(lactic-co-glycolic acid) (PLGA), or polyhydroxyalkanoates (polyhydroxybutyrates and polyhydroxyvalerates and copolymers). In some embodiments, poly(ethylene glycol) (PEG) may be incorporated into the biodegradable polyester to add hydrophilic and other physico-chemical properties to enhance drug delivery. In some embodiments, composites of allograft bone and biodegradable polymers, such as, for example, PLEXURO products available from Osteotech, may be used in the covering.

In some embodiments, the covering may comprise a material that becomes tacky upon wetting. Such material may be, for example, a protein or gelatin based material. Tissue adhesives, including mussel adhesive proteins and cryanocrylates, may be used to impart tackiness to the covering. In further examples, alginate or chitosan material may be used to impart tackiness to the covering. In further embodiments, an adhesive substance or material may be placed on a portion of the covering or in a particular region of the covering to anchor that portion or region of the covering in place at an implant site.

In one embodiment there is a covering comprising two compartments, where first and second materials may be used for the first and second compartments, respectively. The first material may release or expose a growth factor according to a first rate and the second material may release a growth factor according to a second rate. Further, the growth factors released by the first and second compartments may be the same or may be different. For example, an angiogenic growth factor may be provided with the first compartment and an osteoinductive growth factor may be provided with the second compartment.

The implantable composition of the disclosure can be used alone, as bone grafting materials, as scaffolds for bone tissue engineering for repair, augmentation and replacement of bone tissue or as carriers of growth factors, or carriers of genes.

The present disclosure also provides methods for making the implantable composition. In one embodiment, the method comprises combining allograft and non-allograft bone material fibers. The non-allograft bone material is prepared by mixing a bioerodible polymer and a ceramic powder to form a slurry; drying the slurry to form a sheet or block; obtaining fibers by shaving, milling or pressing the sheet or block; embedding within or disposing on the fibers non-fibrous demineralized bone matrix particles. The non-fibrous demineralized bone matrix particles are obtained from the preparation of allograft fibers. These non-allograft fibers are combined with fibers of demineralized bone matrix from allograft bone to form a second slurry; the second slurry is then dried to form a sheet or block; fibers are obtained by shaving, milling or pressing the sheet or block. The fibers are then shaped into a matrix using a binding agent which interlocks the fibers.

Another method for making an implantable composition involves mixing demineralized bone matrix particles with collagen and ceramic powder to form a slurry, drying the slurry to form a sheet or a block, and obtaining fibers from the sheet or block. The method may provide for air-drying or alternatively, freeze drying. The fibers are then combined with fibers of demineralized bone matrix from allograft bone. The combination of fibers are then shaped into a matrix using a binding agent which interlocks the fibers. In some embodiments, the binding agent is glycerol. After combining the bioerodible polymer and the ceramics, the demineralized bone matrix is coated onto the surface.

In some embodiments, cylindrical blocks are formed and long fiber shavings made from the cylinder block on a rotating lathe. The process then follows that for making Grafton matrix which is described in U.S. Pat. No. 5,507,813 and U.S. Pat. No. 6,123,731 each of which is incorporated by reference herein in their entirety.

In some embodiments, the method comprises obtaining the fibers by shaving, milling, or pressing the sheet or block under aseptic conditions. The shape of the fibers can be optimized for inducing new bone formation and handling properties via the network of fibers.

In some embodiments, the method comprises crosslinking the collagen.

In a still further aspect, the present disclosure provides a method of accelerating bone formation at an implantable tissue regeneration scaffold. In a still further aspect, the present disclosure provides a method of regenerating bone in a patient in need thereof, comprising implanting the patient with the implantable composition.

In a still further aspect, the present disclosure provides a method of treating a bone defect caused by injury, disease, wounds, or surgery utilizing an implantable composition comprising a combination of fibers of demineralized bone matrix obtained from allograft bone, and fibers of non-allograft bone material, the fibers of non-allograft bone material comprising non-fibrous demineralized bone particles embedded within or disposed on the fibers of non-allograft bone material.

It should be understood that the forgoing relates to exemplary embodiments of the disclosure and that modifications may be made without departing from the spirit and scope of the disclosure as set forth in the following claims. 

What is claimed is:
 1. An implantable composition comprising a combination of fibers of demineralized bone matrix obtained from allograft bone, and fibers of non-allograft bone material, the fibers of non-allograft bone material comprising non-fibrous demineralized bone matrix particles embedded within or disposed on the fibers of non-allograft bone material.
 2. An implantable composition according to claim 1, wherein the fibers of the non-allograft bone material comprise a bioerodible polymer, and one or more ceramics.
 3. An implantable composition according to claim 2, wherein the bioerodible polymer is collagen, hyaluronic acid, chitosan, keratin, chitin, cellulose, glycosaminoglycans and derivatives thereof, either alone or in combination.
 4. An implantable composition according to claim 3, wherein the bioerodible polymer is collagen.
 5. An implantable composition according to claim 2, wherein the one or more ceramic is a calcium phosphate ceramic and a silicon ceramic.
 6. An implantable composition according to claim 5, wherein the calcium phosphate ceramic is tricalcium phosphate.
 7. An implantable composition according to claim 1, wherein the ratio of fibers of demineralized bone matrix from allograft material to fibers of non-allograft material ranges from about 20:80 to about 70:30.
 8. An implantable composition according to claim 7, wherein the ratio of fibers of demineralized bone matrix from allograft material to fibers of non-allograft material ranges from about 40:60 to about 60:40.
 9. An implantable composition according to claim 1, wherein the demineralized bone matrix particles embedded within or disposed on the fibers of non-allograft bone material comprise from about 10 percent to about 50 percent of the composition by weight.
 10. An implantable composition according to claim 1, wherein the diameter of the fibers of non-allograft material is between about 50 um and about 1 mm.
 11. An implantable composition according to claim 4, wherein the collagen comprises from about 5 percent to about 30 percent by weight of the composition.
 12. An implantable composition according to claim 4, wherein the collagen is porous.
 13. An implantable composition according to claim 1, wherein the fibers of the non-allograft bone material comprise collagen and ceramics is tricalcium phosphate ceramic and silicon ceramic, and demineralized bone matrix particles embedded within or disposed on the fibers of non-allograft bone material.
 14. An implantable composition according to claim 1, further comprising a bioactive agent.
 15. An implantable composition according to claim 1, further comprising a covering.
 16. A method for making an implantable composition according to claim 1, comprising: combining allograft and non-allograft bone material fibers, wherein the non-allograft bone material is prepared by mixing a bioerodible polymer and a ceramic powder to form a slurry; drying the slurry to form a sheet or block; obtaining fibers by shaving, milling or pressing the sheet or block; embedding within or disposing on the fibers non-fibrous demineralized bone matrix particles; preparing non-fibrous demineralized bone matrix particles from the preparation of allograft fibers; combining non-allograft fibers with fibers of demineralized bone matrix from allograft bone to form a second slurry; the second slurry is then dried to form a sheet or block; fibers are obtained by shaving, milling or pressing the sheet or block; and shaping the fibers into a matrix using a binding agent which interlocks the fibers.
 17. The method for making an implantable composition according to claim 16, further comprising adding a bioactive agent.
 18. The method for making an implantable composition according to claim 16, wherein a binding agent is added to the fibers forming a matrix.
 19. A method of generating or regenerating bone in a patient in need thereof, comprising implanting said patient with the implantable composition of claim
 1. 20. A kit for an implantable composition, the kit comprising: a combination of fibers of demineralized bone matrix from allograft bone; fibers of non-allograft bone material, the fibers of non-allograft bone material comprising non-fibrous demineralized bone matrix particles embedded within or disposed on the fibers of non-allograft bone material; and instructions for preparation. 